JPH11188033A - Dental X-ray image capturing apparatus and module for dental X-ray image capturing apparatus - Google Patents

Abstract

(57) [Summary] (with correction) [PROBLEMS] To reduce the size of a tooth image detection unit and generate a trigger pulse stably. SOLUTION: A scintillator, such as a photodiode, which emits light by the incidence of transmitted X-rays transmitted through teeth, a solid-state imaging device for imaging light emission, a base plate on which the solid-state imaging device is arranged, and a base plate arranged on the base plate And a tooth image detecting unit 3 having a photoelectric element for generating a photocurrent, an imaging time control unit 5 having a trigger pulse generating circuit, and an integration time control signal and an electric signal stored in the solid-state imaging device. And a monitor unit 8 connected to the image sensor control unit and displaying an X-ray image of the teeth.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention
The present invention relates to a dental X-ray imaging apparatus capable of automatically adjusting an imaging time of an X-ray image of a tooth according to an irradiation time of a radiation source.

[0002]

2. Description of the Related Art In a dental X-ray imaging apparatus, a filmless system using a solid-state imaging device such as a CCD has been proposed instead of the conventional silver halide film system. Compared to the conventional film method, this filmless method enables real-time observation, does not require any equipment or processing solution for development, and has a linear X-ray sensitivity characteristic of the solid-state image sensor, thus reducing the amount of X-ray irradiation. Image processing of the captured X-ray image, and easy copying and storage of the captured X-ray image.

On the other hand, in the filmless method, since it is necessary to synchronize the X-ray emission timing of the X-ray emission device with the image reading operation of the solid-state imaging device, the X-ray emission timing attached to the X-ray emission device is detected. A cable for connecting the trigger pulse generating circuit to be driven and the drive control unit of the solid-state imaging device is required. That is, the trigger signal from the trigger pulse generation circuit is transmitted to the drive control unit of the solid-state imaging device via this cable, and the drive control unit controls the image reading signal. However, there is a problem in that the presence of this cable complicates the operation of capturing an X-ray image.

In order to solve this problem, there is known a technique in which a trigger pulse generating circuit is not provided in an X-ray emitting device but is provided on a CCD device side. For example, Tokiohei 6-50
In the apparatus disclosed in Japanese Patent Application Laid-Open No. 7796, the trigger pulse generating circuit is disposed on the back of the CCD, that is, on the opposite side of the X-ray source with the CCD interposed therebetween. According to this apparatus, the exposure time can be adjusted according to the time during which the CCD device is irradiated with the X-rays emitted from the X-ray emitting device without using a cable for connecting the X-ray emitting device and the CCD. It becomes possible.

[0005]

In a dental X-ray image pickup device for picking up an X-ray image of a tooth, the tooth image detecting section containing the CCD is used in the oral cavity, so that the tooth image detecting section is small. It is extremely important to improve the ease of use. However, in the device disclosed in Japanese Patent Application Laid-Open No. 6-507796, the trigger pulse generating circuit is provided on the back of the CCD, and as a result, the size of the tooth image detecting unit becomes large, and the patient is inoperable when using the device. It will give you pleasure.

Further, the X-rays transmitted through the CCD enter the photodiode with scintillator and also enter the trigger pulse generating circuit. In the trigger pulse generation circuit,
Further, X-rays enter from the opposite side of the CCD. As described above, when the X-rays enter the trigger pulse generation circuit, the signal amount and signal width of the signal itself generated from the trigger pulse generation circuit may change, or the timing may change. Fluctuations in signals and timing tend to cause malfunctions. Furthermore,
The incidence of X-rays degrades the characteristics of components such as ICs, which are components of the trigger pulse generation circuit, and thus degrades the characteristics of the circuit unit itself.

SUMMARY OF THE INVENTION The present invention has been made to solve such a conventional problem. A dental X-ray imaging apparatus capable of reducing the size of a tooth image detecting section and stably generating a trigger pulse. It is an object to provide a device and a module for a dental X-ray image capturing device.

[0008]

In order to solve the above-mentioned problems, a dental X-ray imaging apparatus according to the present invention provides a scintillator which emits light when a transmitted X-ray transmitted through a tooth as a subject and emits light from the scintillator. For example, a solid-state imaging device such as a CCD, which captures the light, and a base plate on which the solid-state imaging device is disposed, and disposed on the base plate,
A tooth image detecting unit having a photoelectric element such as a photodiode, which generates a photocurrent when light emitted from the scintillator enters, and a trigger for converting the photocurrent output from the photoelectric element into a trigger pulse An imaging time control unit having a pulse generation circuit; an integration time control signal for controlling an imaging time of the solid-state imaging device based on a trigger pulse; and a readout signal for reading out an electric signal accumulated in the solid-state imaging device. An image sensor control means for transmitting to the element, a monitor means connected to the image sensor control means for displaying an X-ray image of the tooth, a tooth image detector and an imaging time controller, and a solid-state image sensor The electric signal accumulated in the optical element and the photocurrent output from the photoelectric element are transferred from the tooth image detection unit to the imaging time control unit, and the imaging time of the solid-state imaging device is controlled. A first cable for transferring a minute time control signal and a readout signal for reading out an electric signal stored in the solid-state imaging device from the imaging time control unit to the tooth image detection unit; an imaging time control unit and an imaging device control unit And transfer the electric signal output from the solid-state imaging device and the trigger pulse output from the imaging time control unit from the imaging time control unit to the imaging device control unit, and store the electric signal stored in the solid-state imaging device. And a second cable for transferring a readout signal for reading out an image and an integration time control signal for controlling the imaging time of the solid-state imaging device from the imaging device control means to the imaging time control section.

According to this dental X-ray image pickup apparatus, an X-ray image of a tooth as a subject can be picked up by a solid-state image pickup device arranged on a base plate via a scintillator. Further, the trigger pulse generating circuit can convert the photocurrent output from the photoelectric element in response to the incidence of X-rays into a trigger pulse. Converted to a signal. The imaging time of the solid-state imaging device is controlled by the integration time control signal.

In particular, according to this dental X-ray image pickup apparatus, a first cable connected to the tooth image detecting section and a second cable connected to the image pickup device control means are provided. Since the imaging time control unit equipped with a trigger pulse generation circuit is arranged between the cables, it is not necessary to arrange the trigger pulse generation circuit in the tooth image detection unit, and the tooth image detection unit can be downsized and the trigger pulse can be stabilized. Can occur.

The electric signal accumulated in the solid-state image sensor is read out by a signal transmitted from the image sensor control means,
The monitor displays an X-ray image of the tooth.

It is desirable that the second cable is thicker than the first cable. The thinner first cable facilitates insertion into the patient's mouth during diagnosis. Also,
If the second cable is thicker, the inner wire is less likely to be cut even when the cable is stepped on by use or a sudden force is applied during use.

Further, it is desirable that two photoelectric elements are arranged with the solid-state image pickup element interposed therebetween. By providing two photoelectric elements, even if one of the photoelectric elements is shielded from the X-ray by the tooth as the subject, the other photoelectric element can output an electric signal for controlling the imaging time. .

The module for a dental X-ray imaging apparatus according to the present invention captures a scintillator that emits light when a transmitted X-ray that has passed through a tooth as a subject and emits light emitted from the scintillator. A solid-state imaging device that outputs a stored electric signal when a readout signal is input, a base plate on which the solid-state imaging device is arranged, and light emitted from a scintillator that is arranged on the base plate and incident thereon A tooth image detection unit having a photoelectric element that generates a photocurrent by generating a photocurrent, and a trigger pulse generation circuit that converts a photocurrent output from the photoelectric element into a trigger pulse that controls the imaging time of the solid-state image sensor. A control unit, which connects the tooth image detection unit and the imaging time control unit, and outputs the electric signal and the photoelectric signal accumulated in the solid-state imaging device. The current is transferred from the tooth image detecting unit to the imaging time control unit, and a readout signal based on a trigger pulse input from the outside and an imaging time of the solid-state imaging device are controlled to read out an electric signal stored in the solid-state imaging device. A first cable for transferring an integration time control signal based on a trigger pulse input from the outside to the tooth image detection unit from the imaging time control unit, and connected to the imaging time control unit,
The electric signal output from the solid-state imaging device and the trigger pulse output from the imaging time control unit are transferred from the imaging time control unit to the outside, and the readout signal and the integration time control signal input from the outside are transferred to the imaging time control unit. And a second cable for transferring the data to the second cable.

By using the module for a dental X-ray image pickup apparatus, an X-ray image of a tooth as a subject can be picked up by a solid-state image pickup device arranged on a base plate via a scintillator. Further, the trigger pulse generation circuit can convert a photocurrent output from the photoelectric element in response to the incidence of X-rays into a trigger pulse which is a basis of an integration time control signal for controlling an imaging time of the solid-state imaging element. it can.

In particular, according to the dental X-ray image capturing apparatus module, the image capturing time control section including the trigger pulse generating circuit is provided between the first cable and the second cable connected to the tooth image detecting section. With this arrangement, it is not necessary to dispose a trigger pulse generating circuit in the tooth image detecting section, so that the tooth image detecting section can be downsized and a trigger pulse can be generated stably.

It is desirable that the second cable is thicker than the first cable. The thinner first cable facilitates insertion into the patient's mouth during diagnosis. Also,
If the second cable is thicker, the inner wire is less likely to be cut even when the cable is stepped on by use or a sudden force is applied during use.

Furthermore, it is desirable that two photoelectric elements are arranged with the solid-state image pickup element interposed therebetween. By providing two photoelectric elements, even if one of the photoelectric elements is shielded from the X-ray by the tooth as the subject, the other photoelectric element can output an electric signal for controlling the imaging time. .

[0019]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Preferred embodiments of a dental X-ray imaging apparatus and a module for a dental X-ray imaging apparatus according to the present invention will be described in detail below. First, dental X
The configuration of the line image capturing device will be described.

FIG. 1 is a diagram showing a dental X-ray imaging apparatus used for diagnosing teeth. An X-ray source 1 that emits X-rays and a sensor head 3 that is a tooth image detecting unit provided at the tip of an imaging device module 2 are set so as to face each other across a patient's teeth 1a. The tooth image detecting unit 3 includes a control box 5 that is an imaging time control unit that controls an imaging time of an X-ray image of the tooth 1 a by the first cable 4.
Is connected. Further, a control device 7 serving as an image sensor control means is connected to the control box 5 via a second cable 6. A monitor 8 for displaying an X-ray image of a tooth and a printer 9 for outputting the display contents are connected to the control device 7.

FIG. 2 is an overall plan view of the imaging device module 2. The sensor head 3 has a CCD and the like described later mounted inside a resin case 3a. The X-ray receiving surface 3b of the sensor head 3 has a substantially rectangular shape having a radius at a corner. The X-ray receiving surface 3b is not limited to the substantially rectangular shape shown in the figure, but may be a circle, an ellipse, a square, or the like. The control box 5 has a rectangular parallelepiped shape, and has
A trigger pulse generation circuit and a buffer circuit described later are mounted.

Sensor head 3 and control box 5
Is smaller in diameter than the second cable 6. In the present embodiment, the diameter of the first cable 4 is about 3 mm, and the diameter of the second cable 6 is about 6 mm, but is not limited to this dimension. The length of the first cable 4 is about 20 cm
The length of the second cable 6 is about 5 m. However, the length is not limited to this, and depends on the environment such as the size of the sensor head 3 and the size of the diagnostic room for diagnosing teeth. Is done.

However, if the first cable 4 is longer than necessary, the cable itself functions as an antenna, so that electromagnetic noise from a peripheral device such as an X-ray generator or a signal (noise) from another cable is used. ). Further, as will be described later, the trigger pulse generating circuit includes an IV converter constituted by an operational amplifier. However, if the first cable is too long, the operational amplifier may oscillate. .

On the other hand, if the length of the first cable 4 is too short, that is, if the distance between the sensor head 3 and the control box 5 is too short, the control box 5 may interfere with the use of the cable, Box 5
Since the inner circuit portion is directly susceptible to X-ray radiation, it may cause a malfunction or the circuit itself may be deteriorated.

Therefore, in consideration of the stability of the output of the trigger pulse generating circuit and the prolongation of the service life, the first cable 4 is not affected by noise and is hindered during use and is affected by X-rays. It is desirable to design it to a length that is not so long. In this case, it is necessary to adjust the length of the second cable 6 to cope with the environment such as the size of the diagnostic room. Therefore, it is desirable that the second cable 6 be longer than the first cable 4. The second cable 6
At one end, a connector 10 for connecting the control device 7 and the imaging device module 2 is provided.

Next, the internal structure of the sensor head 3 will be described with reference to FIGS. FIG. 3 shows the sensor head 3
4 is a plan view of the inside of the sensor head 3. FIG. Ceramic fixed base 1
A base plate 12 made of copper-tungsten is provided substantially at the center of the base 1, and a CCD 14 is adhered on the base plate 12 by a conductive resin. The wiring of the CCD 14 is drawn out from one of the four sides, and
Is formed. Then, on each of two sides perpendicular to the side on which the wiring portion 15 is provided, one strip-shaped photodiode 16 is provided with the CCD 14 interposed therebetween. In addition,
The base plate 12 is not limited to a material made of copper tungsten, and may be any material that can form a flat film with high precision.

An optical fiber plate 17 is fixed above the CCD 14 and the photodiodes 16 with an adhesive resin so as to cover them. Above the optical fiber plate 17, a scintillator 18 made of GOS (gadmium oxysulfide) is arranged. Note that the scintillator 18 is not limited to GOS, but may use NaI, CsI, or the like. The optical fiber plate 17 can transmit the optical image converted by the scintillator to the light receiving surface of the CCD 14 without diffusing. On the other hand, three layers of ceramic layers 13 are stacked on three sides of the fixing base 11 other than the side where the wiring portion 15 of the CCD 14 is provided. Since only the uppermost layer of the three ceramic layers 13 protrudes toward the optical fiber plate 17, even if the lower two layers are misaligned when the ceramic layers 13 are stacked, The optical fiber plate 17 can be accurately fixed to the CCD 14 by adjusting the position of the protrusion of the layer.

The sensor head 3 according to the present embodiment
Although the CCD 14 and the band-shaped photodiode 16 are formed separately on the base plate 12 as described above, the CCD 14 and the band-shaped photodiode 16 may be formed monolithically on the silicon substrate of the CCD. it can. When the CCD 14 and the band-shaped photodiode 16 are formed in a monolithic manner, they can be arranged closer to each other, so that further miniaturization can be realized and the entire device can be manufactured at lower cost. Further, since the CCD 14 and the photodiode 16 can be formed on the silicon substrate by the same process, the manufacturing process does not become complicated. Furthermore, placing the CCD 14 and the photodiode 16 on the base plate 12 respectively,
Since there is no need to perform alignment between the two, the assembly process can be simplified.

Next, a process of diagnosing teeth using the dental X-ray imaging apparatus according to the present embodiment will be described with reference to FIGS. First, the sensor head 3 is brought into contact with the back side of the tooth 1a to be diagnosed by a patient, a switch (not shown) of the X-ray source 1 is turned on for a certain time, and X-rays are emitted toward the tooth 1a. The transmitted X-ray transmitted through the tooth 1a enters the scintillator 18 of the sensor head 3. Scintillator 1
Numeral 8 emits photons when transmitted X-rays enter.
The emitted photons travel through the fiber optic plate 17 and
By arriving at the CD 14, the CCD 14 receives the X of the tooth 1a.
A line image can be captured. When photons emitted from the scintillator 18 enter the CCD 14, the CCD 14
The signal charges are accumulated in 14. Tooth 1 due to tooth decay
When there is a cavity in a part of a, the amount of X-rays transmitted through the cavity becomes large, so that the amount of photons emitted by the scintillator 18 becomes large as compared with a part without a cavity, and furthermore, , The amount of signal charges stored in the CCD 14 also increases.

Here, the CCD 14 will be described with reference to FIGS.
A method for controlling the imaging time will be described. In this embodiment, one cycle of the imaging operation (time) of the CCD 14 includes an operation (time) of accumulating signal charges, an integration operation (time) called an exposure operation, and a reading operation (time) of reading out signal charges. You.

FIG. 5 shows a flow from X-ray irradiation to monitor display of an X-ray image. As shown in FIG. 5, photons generated by irradiating the scintillator 18 with X-rays and transmitted X-rays are incident not only on the CCD 14 but also on two photodiodes 16. When a photon is incident on the photodiode 16, the photodiode 16 generates a photocurrent, which travels through the first cable 4 and reaches a trigger pulse generation circuit 19 in the control box 5. In the case where the number of the photodiodes 16 is one, even if the diode is irradiated with X-rays, malfunctions such as generation of no photocurrent occur when the diodes are stained with teeth or shadows of gold teeth. By providing two, even if one of the photodiodes 16 is shaded, malfunction can be prevented.

FIG. 6 shows a configuration of the trigger pulse generation circuit 19, and FIG. 7 is a timing chart of the trigger pulse generation circuit 19. Note that (I) to (V) in FIG.
I) shows the signals in (I) to (VI) of FIG. As shown in FIG. 6, the trigger pulse generation circuit 19
-V converter 19a, amplifier circuit 19b, comparator 19
c, monostable multivibrator 19d, inverter 19
e.

The photocurrent that has reached the trigger pulse generating circuit 19 is converted into a voltage by an IV converter 19a as shown in FIG. 7 (II). This output voltage is supplied to the amplifying circuit 19b.
Amplified by several times as shown in (III), the comparator 19c
Then, as shown in FIG. 7 (IV), the analog signal is converted into a digital signal such as TTL. Then, the monostable multivibrator 19d stretches it to a predetermined width as shown in FIG.
After being inverted as in I), a trigger pulse is output to the control device 7.

[0034] The control device 7 determines, based on the trigger pulse,
C is set so that the integration of the X-ray image of the tooth 1a starts at the falling portion of the trigger pulse and ends at the rising portion.
An integration time control signal for controlling the CD is determined, and this signal is output to the CCD. Further, the control device 7 determines a read signal for reading the signal charge of the CCD 14 based on the trigger pulse, and continuously outputs this signal to the CCD.

Conventionally, the trigger pulse generating circuit 19 which fulfills such a function is housed in the sensor head 3, but as in the present embodiment, the control box 5 is provided outside the sensor head 3, and the control box 5 is provided therein. By accommodating the trigger pulse generating circuit 19, the size of the sensor head 3 can be reduced. The trigger pulse generation circuit 19
Is less likely to be directly irradiated with X-rays, so that malfunction of a circuit due to X-ray incidence and deterioration of the circuit portion itself can be prevented.

The provision of the control box 5 outside the sensor head 3 makes it possible to use two cables having different thicknesses, that is, a first cable 4 and a second cable 6. In diagnosing the tooth 1a, as shown in FIG. 8, not only the sensor head 3 but also a part of the first cable 4 enters the oral cavity.
Since the first cable 4 has a small diameter, it can be smoothly inserted into the oral cavity. Also, in view of being used in the oral cavity, it is desirable that the first cable 4 be formed of a flexible material.

On the other hand, the second cable 6 connected to the control device 7 is often placed on the floor, but in the present embodiment, the diameter of the second cable 6 is made large, Even when the cable is entangled with the foot or stepped on, the wiring in the cable is hard to be cut. That is, conventionally, a control box 5 that houses a trigger pulse generation circuit is used.
Therefore, the diameter of the cable connecting the sensor head and the control device had to be constant, but according to the present embodiment, since the control box 5 was provided, it was easy to insert into the oral cavity, It is possible to simultaneously improve both the difficulty of cutting the wiring.

Next, a process until an X-ray image picked up by the CCD 14 is displayed will be described. CCD from controller 7
When the above-described read signal for reading the signal charges stored in the memory 14 is transmitted, the read signal is transmitted to the second cable 6,
The control box 5 further travels through the first cable 4 and reaches the CCD 14.

When the read signal reaches the CCD 14, CC
The signal charge stored in D14 is read. The signal charge travels through the first cable 4 as an electric signal and reaches the control box 5. The signal charge generated by the CCD 14 is converted into a voltage signal by a MOSFET (not shown) at the output of the CCD 14 and a load resistor provided inside the control box 5.

After that, the output impedance of the electric signal converted into the voltage signal is reduced by the buffer circuit provided inside the control box 5, so that the electric signal is less affected by noise, and the second cable having a large diameter is used. The signal does not deteriorate even when the signal propagates through 6. The electric signal that has passed through the buffer circuit travels through the second cable 6 and reaches the control device 7. The electric signal is subjected to computer processing in the control device 7, and an X-ray imaging result of the tooth 1 a is displayed on the monitor 8.

At this time, a portion having a cavity due to tooth decay or the like,
That is, a portion having a large amount of signal charge stored in the CCD 14 can be displayed in a dark color, and a portion having no cavity, that is, a portion having a small amount of signal charge, can be displayed in a light color. Further, by changing the computer processing method in the control device 7, it is possible to make a portion having a large amount of signal charges a bright color and a portion having a small amount of signal charges a dark color. Also,
The display result on the monitor 8 is output by the printer 9.

[0042]

According to the dental X-ray image capturing apparatus of the present invention, a first cable connected to the tooth image detecting section and a second cable connected to the image sensor controlling means are provided.
Since the imaging time control unit including the trigger pulse generation circuit is arranged between the two cables, it is not necessary to arrange the trigger pulse generation circuit in the tooth image detection unit, and the tooth image detection unit can be downsized and the trigger can be reduced. Pulses can be generated stably.

Further, by making the first cable thinner than the second cable, it is possible to easily insert the first cable into the patient's mouth during diagnosis. In addition, if the second cable is made thicker, it is possible to make it difficult for the internal line to be cut even when the cable is stepped on with a foot or a sudden force is applied during use.

Further, by providing two photoelectric elements, even if one of the photoelectric elements is shielded from the incidence of X-rays by dirt on the teeth or gold teeth, the other photoelectric element controls the imaging time. A signal can be output.

[Brief description of the drawings]

FIG. 1 is a view showing one embodiment of a dental X-ray image capturing apparatus according to the present invention.

FIG. 2 is an overall plan view showing one embodiment of a module for a dental X-ray image capturing apparatus according to the present invention.

FIG. 3 is a longitudinal sectional view of the inside of a sensor head of the dental X-ray image capturing apparatus.

FIG. 4 is a plan view showing the inside of a sensor head of the dental X-ray image capturing apparatus.

FIG. 5 is a flowchart from X-ray irradiation to monitor display of an X-ray image.

FIG. 6 is a configuration diagram of a trigger pulse generation circuit.

FIG. 7 is a timing chart of the trigger pulse generation circuit.

FIG. 8 is an enlarged view showing a use state of the dental X-ray image capturing apparatus.

[Explanation of symbols]

DESCRIPTION OF SYMBOLS 1 ... X-ray source, 2 ... module for imaging devices, 3 ... sensor head (tooth image detection part), 4 ... first cable, 5 ... control box (imaging time control part), 6 ... second cable, 7 ... Control device (imaging element control means), 14 CC
D, 16: photodiode, 17: optical fiber plate, 18: scintillator, 19: trigger pulse generation circuit.

Claims (6)

[Claims] 1. A scintillator that emits light by incidence of transmitted X-rays that have passed through a tooth as a subject, a solid-state imaging device that captures light emitted from the scintillator, and a base plate on which the solid-state imaging device is disposed. A tooth image detection unit that is disposed on the base plate and has a photoelectric element that generates a photoelectric current when light emitted from the scintillator is incident thereon, and the photoelectric current output from the photoelectric element. An imaging time control unit having a trigger pulse generation circuit that converts the signal into a trigger pulse; an integration time control signal that controls an imaging time of the solid-state imaging device based on the trigger pulse; and an electric signal accumulated in the solid-state imaging device. An image sensor control means for transmitting a read signal for reading to the solid-state image sensor; and Monitor means for displaying an X-ray image, and connecting the tooth image detection unit and the imaging time control unit, and the electric signal accumulated in the solid-state imaging device and the photocurrent output from the photoelectric device. Is transferred from the tooth image detection unit to the imaging time control unit, the integration time control signal for controlling the imaging time of the solid-state imaging device and the read signal for reading the electric signal accumulated in the solid-state imaging device, A first cable for transferring the imaging time control unit to the tooth image detection unit, and connecting the imaging time control unit and the imaging device control unit, and the electric signal output from the solid-state imaging device. Transferring the trigger pulse output from the imaging time control unit to the imaging device control unit from the imaging time control unit, and reading out the electric signal accumulated in the solid-state imaging device And a second cable for transferring the readout signal and the integration time control signal for controlling the imaging time of the solid-state imaging device from the imaging device control means to the imaging time control unit. Dental X-ray imaging device. 2. The dental X-ray imaging apparatus according to claim 1, wherein the second cable is thicker than the first cable. 3. The dental X-ray imaging apparatus according to claim 1, wherein two photoelectric elements are arranged with the solid-state imaging element interposed therebetween. 4. A scintillator that emits light when a transmitted X-ray that has passed through a tooth as a subject is emitted, and an electric signal that is captured by capturing a light emitted from the scintillator and inputting a readout signal from outside. A solid-state imaging device that outputs a solid-state imaging device, a base plate on which the solid-state imaging device is arranged, and a photoelectric device that is arranged on the base plate and generates a photocurrent when light emitted from the scintillator enters. An imaging time control unit having a trigger pulse generation circuit that converts the photocurrent output from the photoelectric element into a trigger pulse that controls the imaging time of the solid-state imaging device; and the tooth image. While connecting the detection unit and the imaging time control unit, the electric signal accumulated in the solid-state imaging device and the output from the photoelectric device And the readout signal based on the trigger pulse input from the outside to transfer the current from the tooth image detection unit to the imaging time control unit and read out the electric signal stored in the solid-state imaging device. A first cable for transferring an integration time control signal based on the trigger pulse input from the outside to control an imaging time of an element from the imaging time control unit to the tooth image detection unit; and the imaging time control unit. Connected to the solid-state imaging device, and transfers the electric signal output from the solid-state imaging device and the trigger pulse output from the imaging time control unit to the outside from the imaging time control unit, and reads the read signal input from the outside. A second cable for transferring a signal and the integration time control signal to the imaging time control unit. A module for a dental X-ray imaging apparatus, comprising: Le. 5. The module for a dental X-ray imaging apparatus according to claim 4, wherein the second cable is thicker than the first cable. 6. The module for a dental X-ray imaging apparatus according to claim 4, wherein two photoelectric elements are arranged with the solid-state imaging element interposed therebetween.